US9199027B2 - Apparatus for extracorporeal blood treatment - Google Patents

Apparatus for extracorporeal blood treatment Download PDF

Info

Publication number
US9199027B2
US9199027B2 US14/006,789 US201214006789A US9199027B2 US 9199027 B2 US9199027 B2 US 9199027B2 US 201214006789 A US201214006789 A US 201214006789A US 9199027 B2 US9199027 B2 US 9199027B2
Authority
US
United States
Prior art keywords
value
control
infusion
target
line
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active, expires
Application number
US14/006,789
Other languages
English (en)
Other versions
US20140088483A1 (en
Inventor
Francesco Fontanazzi
Alessandro Surace
Francesco Paolini
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gambro Dasco SpA
Original Assignee
Gambro Dasco SpA
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Gambro Dasco SpA filed Critical Gambro Dasco SpA
Assigned to GAMBRO DASCO S.P.A. reassignment GAMBRO DASCO S.P.A. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: FONTANAZZI, FRANCESCO, PAOLINI, FRANCESCO, SURACE, Alessandro
Publication of US20140088483A1 publication Critical patent/US20140088483A1/en
Application granted granted Critical
Publication of US9199027B2 publication Critical patent/US9199027B2/en
Active legal-status Critical Current
Adjusted expiration legal-status Critical

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1601—Control or regulation
    • A61M1/1603—Regulation parameters
    • A61M1/1605—Physical characteristics of the dialysate fluid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1601—Control or regulation
    • A61M1/1613—Profiling or modelling of patient or predicted treatment evolution or outcome
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/3403—Regulation parameters
    • A61M1/341—Regulation parameters by measuring the filtrate rate or volume
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3317—Electromagnetic, inductive or dielectric measuring means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3324—PH measuring means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • A61M2205/3393—Masses, volumes, levels of fluids in reservoirs, flow rates by weighing the reservoir
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/502—User interfaces, e.g. screens or keyboards
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/52—General characteristics of the apparatus with microprocessors or computers with memories providing a history of measured variating parameters of apparatus or patient

Definitions

  • the present invention relates to an apparatus for extracorporeal blood treatment.
  • Apparatus for extracorporeal blood treatment comprise at least one treatment unit (for example a dialyser or a filter or ultrafilter or a plasma filter or a filtering unit of another type) having a semipermeable membrane which separates the treatment unit into two chambers.
  • An extracorporeal blood circuit enables circulation of blood removed from a patient internally of the first chamber.
  • a treatment fluid is made to circulate through an appropriate circuit in the second chamber of the treatment unit.
  • This type of apparatus for blood treatment known as dialysis apparatus, can be used for removal of excess solutes and fluids from the blood of patients suffering from kidney failure.
  • a particular type of apparatus for blood treatment known as hemofiltration or hemodiafiltration apparatus, comprises the presence of an infusion line predisposed to sent a replacement fluid into the extracorporeal blood circuit.
  • the infusion line or lines are connected upstream and/or downstream with respect to the treatment unit.
  • the above-described blood treatment apparatus can be controlled in various ways.
  • the apparatus can be controlled volumetrically, such as to have predetermined flow rates along the various fluid transport lines.
  • the apparatus can be controlled such that the transmembrane pressure (herein indicated as TMP) follows a set value.
  • TMP transmembrane pressure
  • Application WO2005IB01482 illustrates an apparatus and a process for setting the TMP value at a level which is such as to maximise the ultrafiltration flow rate and consequently the volume of fluid infused into the patient. This solution is advantageous as it maximises the flow rate of ultrafiltration and infusion, and thus maximises the convective exchange through the membrane and thus the purification of the blood from undesired particles.
  • An aim of the present invention is to make available an apparatus for blood treatment which is able to operate efficiently even in the presence of high convective exchange, i.e. in the presence of infusion lines for infusing relatively high quantities of replacement fluid during treatment and guaranteeing at the same time a high degree of patient comfort.
  • a further aim of the present invention is to make available an apparatus which is able to control convective exchange and contemporaneously also control weight loss and plasma conductivity and sodium concentration, to be delivered to the patient under treatment.
  • An additional aim of the present invention is to provide an apparatus which is able to determine a setting value of TMP in a way which is simple and rapid and which is capable, if possible, of increasing the volume of liquid exchanged with the patient, while avoiding conflicts with any other controls aimed at improving the comfort of the patient during treatment.
  • a further aim of the invention is to provide an apparatus which, though accelerating the search sequence for the TMP setting, is however able to operate safely.
  • At least one of the above-indicated aims is substantially attained by an apparatus for blood treatment as in one or more of the appended claims.
  • an apparatus for extracorporeal blood treatment comprises: at least one treatment unit, having at least one first chamber and at least one second chamber, separated from one another by a semipermeable membrane, at least one blood removal line connected to an inlet port of the first chamber and predisposed to remove blood from a patient, at least one blood return line connected with an outlet port of the first chamber and predisposed to return treated blood to the patient (the blood removal line, the blood return line and the first chamber being part of an extracorporeal blood circuit), at least one infusion line of a replacement fluid connected with the extracorporeal circuit or directly connectable with a patient and, optionally, a dialysis line connected in inlet to the second chamber, at least one fluid evacuation line connected to an outlet port of the second chamber, and sensor means.
  • the sensor means are positioned and configured such as to determine:
  • the apparatus further comprises a control unit connected with the sensor means and configured such as to perform a control procedure comprising:
  • a 2 nd aspect comprises an apparatus for extracorporeal blood treatment comprising:
  • At least one treatment unit having at least one first chamber and at least one second chamber, separated from one another by a semipermeable membrane, at least one blood removal line connected to an inlet port of the first chamber and predisposed to remove blood from a patient, at least one blood return line connected to an outlet port of the first chamber and predisposed to return treated blood to the patient (the blood removal line, the blood return line and the first chamber being part of an extracorporeal blood circuit), at least one infusion line of a replacement fluid connected to the extracorporeal circuit or directly connectable with a patient and, optionally, a dialysis line connected in inlet to the second chamber, at least one fluid evacuation line connected with an outlet port of the second chamber, and sensor means.
  • the sensor means are positioned and configured such as to determine:
  • the apparatus further comprises a control unit connected to the sensor means and configured such as to perform a control procedure comprising:
  • control procedure comprises setting the control values during a time interval ⁇ t subsequent to the control instant t.
  • control unit is configured or programmed such as to repeat the control procedure at control instants t which are temporally consecutive of one another.
  • control values are calculated on the basis of:
  • control values are calculated on the basis of:
  • control values are also calculated on the basis of a prescription value of a volume to be infused in the patient V INFtarget by the end of treatment.
  • control values are also calculated on the basis of a prescription flow rate of a volume to be infused in the patient Q INFtarget during the treatment.
  • the apparatus comprises a first regulating device for regulating an ultrafiltration rate or a transmembrane pressure between the first and the second chamber of the treatment unit, the first regulating device being connected to the control unit and being active on at least one of the extracorporeal blood circuit and fluid evacuation line.
  • the apparatus comprises a second regulating device for regulating a composition of the dialysis liquid and/or the replacement liquid, the second regulating device being connected to the control unit and being active on the dialysis line and/or on the infusion line for regulating the conductivity or sodium concentration Cd, Na of the liquid crossing the dialysis line and/or the infusion line.
  • the step of setting the control values during the procedure comprises:
  • the apparatus comprises at least one infusion pump, or another regulating device of the fluid flow along the infusion line or lines, active on the infusion line and connected to the control unit for causing an infusion liquid flow along the line and wherein the control unit is configured such as to control the infusion pump and the first regulating device such as to impose both the control value relating to the weight loss rate WLR (t) and the control value relating to the infusion line Q INF(t) .
  • the regulation of the infusion rate especially if concerned with a replacement fluid line located upstream of the treatment unit, can also be regulated in accordance with the transmembrane pressure membrane TMP (t) .
  • control unit is configured such as to command the second regulating device in order to impose the control parameter relating to the conductivity or sodium concentration Cd (t) , Na (t) and to the liquid crossing the dialysis line and the liquid crossing the infusion line.
  • control procedure uses a mathematical model M, representing kinetics of the solutes in a distribution volume in the patient, in order to determine an equivalent sodium concentration value Na eq(t) at the control instant t, the model being memorised in a memory associated to the control unit, the control unit being configured such as to apply the following values in inlet to the mathematical model:
  • an estimated total convective and diffusive clearance value Cl mes(t) is calculated on the basis of a current measured value of the infusion flow rate Q INFmes(t) and one from among current measured value of blood flow Q Bmes(t) and a current diffusive clearance value Cl diff(t) .
  • the estimated total convective and diffusive clearance value Cl mes(t) can be mathematically extrapolated from preceding values assumed by CI.
  • the mathematical model is representative of a kinetics of the solutes in a distribution volume in the patient, optionally according to a single-compartment model.
  • control procedure comprises also using the equivalent sodium concentration parameter at the instant t (i.e. Na eq(t) ) for determining the control values.
  • control procedure comprises the following sub-steps:
  • control procedure comprises the sub-steps of:
  • control sodium conductivity or concentration value Cd (t) , Na (t) to impose on the liquid crossing the dialysis line and/or the infusion line is calculated on the basis of the second error parameter ERR_BV_Na (t) and on the basis of the conductivity or sodium concentration value Cd (t- ⁇ t) , Na (t- ⁇ t) relating to the preceding control instant.
  • control flow rate value to be imposed for the weight loss rate WLR (t) is calculated on the basis of the first error parameter ERR_BV_UF (t) and on the basis of the ultrafiltration flow rate UFR (t- ⁇ t) relating to the preceding control instant.
  • control unit is configured for:
  • commanding the infusion of the bolus comprises imposing a predetermined flow for a predetermined time of administration to the infusion pump.
  • control unit is configured for setting, during administration of the bolus, an ultrafiltration flow rate value of zero.
  • commanding the infusion of the bolus comprises commanding, during administration of the bolus, the second regulating device of the liquid composition such as to impose a predetermined value on the conductivity or sodium concentration Cd (t) , Na (t) on the liquid crossing the infusion line.
  • the sensor means comprise at least one first sensor S 7 acting on the extracorporeal circuit for detecting the variation BV % of the blood volume of the patient.
  • the sensor means comprise at least one second sensor S 6 active on the evacuation line for determining the ultrafiltration rate UFR across the membrane, or the weight loss rate WLR of the patient, or an accumulated weight loss WL.
  • the sensor means comprise at least one third sensor S 8 active on the dialysis line or on the infusion line or on a common supply line of the dialysis line and the infusion line, the third sensor being a conductivity or concentration sensor predisposed for determining the conductivity of a liquid crossing the dialysis line and/or the infusion line or the sodium concentration of the liquid crossing the dialysis line and/or the infusion line.
  • the sensor means comprise at least one fourth sensor S 5 for determining an infusion rate Q INF of the replacement fluid crossing the infusion line and at least one fifth pressure sensor S 1 , S 2 , S 3 , S 4 for determining a transmembrane pressure TMP between the first and the second chamber.
  • a 30 th aspect concerns an apparatus for extracorporeal blood treatment comprising at least one treatment unit having at least one first chamber and at least one second chamber separated from one another by a semipermeable membrane; at least one blood removal line connected to an inlet port of the first chamber and predisposed for removing blood from a patient; at least one blood return line connected with an outlet port of the first chamber and predisposed to return treated blood to the patient.
  • the blood removal line, the blood return line and the first chamber are part of an extracorporeal blood circuit of the apparatus.
  • the apparatus also exhibits at least one infusion line of a replacement fluid connected with the extracorporeal circuit or directly connectable to a patient;
  • At least one dialysis line connected in inlet to the second chamber; at least one fluid evacuation line connected with an outlet port of the second chamber; and sensor means for determining:
  • the apparatus comprises a first regulating device active on at least one of the extracorporeal circuit and the fluid evacuation line and configured such as to regulate an ultrafiltration flow rate UFR or a transmembrane pressure TMP between the first and the second chamber of the treatment unit, and a control unit connected with the sensor means and with the first regulating device and configured such as to perform a control procedure in order to regulate the weight loss rate and at least one setting sequence for maximising the convective exchange across the semipermeable membrane.
  • a first regulating device active on at least one of the extracorporeal circuit and the fluid evacuation line and configured such as to regulate an ultrafiltration flow rate UFR or a transmembrane pressure TMP between the first and the second chamber of the treatment unit
  • a control unit connected with the sensor means and with the first regulating device and configured such as to perform a control procedure in order to regulate the weight loss rate and at least one setting sequence for maximising the convective exchange across the semipermeable membrane.
  • control unit is programmed or configured such as to perform, at least at a control instant t, a control procedure comprising:
  • control unit is further programmed or configured such as to perform at least one setting instant ⁇ and a setting sequence of the transmembrane pressure, the setting sequence comprising:
  • the sensor means are predisposed to determine at least one fifth parameter Cd, Na relating to a conductivity of a liquid crossing the dialysis line and/or the infusion line or at a sodium concentration (or a predetermined other substance to be monitored) of the liquid crossing the dialysis line and/or the infusion line.
  • the step of receiving comprises receiving, from the sensor means, measured values of the:
  • the control procedure includes that the step of calculating comprises calculating, in accordance with the measured values and prescription values of variation of blood volume BV % target , of the weight loss WL target and the plasma conductivity or sodium concentration in the patient (or alternatively the infusion volume V INFtarget of a transmembrane pressure value TMP target to be followed in a predetermined treatment time), the following control values: get to
  • the control procedure comprises that the step of imposing comprises imposing the control value relating to the conductivity or sodium concentration Cd (t) , Na (t) and the value relating to the weight loss rate WLR (t) .
  • control unit is configured such as to perform the control procedure at a plurality of control instants t that are temporally reciprocally successive.
  • control unit is configured such as to impose the control values during a time interval ⁇ t after each control instant t.
  • control unit is configured such as cyclically to repeat the control procedure during the whole treatment.
  • control unit is configured such as to perform the setting sequence at a plurality of setting instants ⁇ temporally successive to one another, and wherein the control unit is configured such as to perform the control procedure at more frequent control instants with respect to the setting instants in which the setting sequence is performed.
  • the setting sequence comprises:
  • control unit is configured such as to calculate an (n+1) th increase ⁇ TMP n+1 as a function of the ultrafiltration flow rate variation ⁇ UFR n corresponding to the nth transmembrane pressure increase ⁇ TMP n and the value of the n th transmembrane pressure increase ⁇ TMP n .
  • K is the relation between the value of the n th transmembrane pressure increase ( ⁇ TMP n ) and the value of a correction factor, optionally wherein the value of the correction factor is selected from among the group comprising:
  • the apparatus comprises at least one user interface, connected to the control unit, the user interface being configured such as to receive command signals entered by a user via the user interface.
  • control unit is configured such as to receive a start command of the setting sequence and/or the control procedure following a command that can be entered by a user acting on a manual activation element of the interface.
  • control unit is configured to start the sequence and/or the procedure automatically.
  • control unit is programmed to:
  • the duration of the time intervals T 1 , T 2 , T n is not uniform, optionally in which the duration of each time interval subsequent to the first is greater than the duration of a time interval preceding it.
  • control unit is programmed such that during the setting sequence, following each command for increase of the transmembrane pressure, a time transitory T r is included before performing a subsequent increase in transmembrane pressure.
  • the duration of the time transitory T r is not uniform.
  • the control unit in a 53 rd aspect according to any one of the aspects from the 30 th to the 52 nd , is predisposed to verify whether between a pressure increase and the successive one there has been a variation in weight loss rate ⁇ WLR imposed by the control procedure and, if the response is affirmative, to prolong the duration of the time transitory T r such that at least one predetermined auxiliary time delay has passed since the last weight loss rate variation.
  • the control unit is predisposed to verify whether between a pressure increase and a next pressure increase there has been a variation in the weight loss rate ⁇ WLR imposed by the control procedure and, if the response is affirmative, the control unit is programmed to prolong a duration of a time transitory T r between a transmembrane pressure increase and a following transmembrane pressure increase, such that at least one predetermined auxiliary temporal delay has passed since the last weight loss rate variation before effecting a new pressure increase.
  • auxiliary temporal delay being less than a temporal delay between a control procedure and a next control procedure.
  • control unit is predisposed to calculate the time transitory T r as a function of the pressure increase between a transmembrane pressure value TMP n and a next TMP n+1 .
  • control unit is predisposed to calculate the time transitory T r as a function of the variation of the weight loss rate ⁇ WLR imposed by the control procedure between a pressure increase and a next pressure increase.
  • control unit is programmed such that during the setting sequence each step of comparison of the value of the ultrafiltration flow rate variation ⁇ UFR 1 ; ⁇ UFR n with a respective reference value ⁇ UFR ref is performed after the time transitory T r , with the aim of enabling a stabilising of the value of the ultrafiltration flow variation.
  • control unit is configured such as to determine the variation of the ultrafiltration flow rate variation ⁇ UFR (n) between a transmembrane pressure variation ⁇ TMP n and a next ⁇ TMP n+1 as a sum of the replacement liquid flow rate variation along the infusion line ⁇ Q INF(n) and the weight loss rate ⁇ WLR (n) that have been verified and measured in a time duration between the transmembrane pressure variation ⁇ TMP n and the next ⁇ TMP n+1 .
  • control value or values are also calculated in accordance with a measured value of replacement fluid flow rate Q INFmes(t) along the infusion line.
  • control values are calculated also in accordance with a prescription value of volume to be infused in the patient V INFtarget by end of treatment.
  • control values are calculated also in accordance with a prescription value of flow rate to be infused in the patient Q INFtarget during treatment.
  • the apparatus comprises a first regulating device for regulating the ultrafiltration or transmembrane pressure between the first and the second chamber of the treatment unit, the first regulating device being connected to the control unit and being active on at least one of the extracorporeal circuit and the fluid evacuation line.
  • the apparatus comprises a second regulating device for regulating a composition of the dialysis liquid and/or the replacement liquid, the second regulating device being connected to the control unit and being active on the dialysis line and/or the infusion line such as to regulate the sodium conductivity or concentration Cd, Na of the liquid crossing the dialysis line and/or the infusion line.
  • the step of imposing the control values during the procedure comprises:
  • the apparatus comprises at least one infusion pump active on the infusion line and connected to the control unit such as to cause an infusion liquid flow rate along the line and wherein the control unit is configured such as to control the infusion pump and the first regulating device such as to impose both the control value relating to the weight loss rate WLR (t) and the control value relating to the infusion flow rate Q INF(t) or the transmembrane pressure TMP (t) .
  • control unit is configured to command the second regulating device to impose the same control value relating to the sodium conductivity or concentration Cd (t) , Na (t) and on the liquid crossing the dialysis line and the liquid crossing the infusion line.
  • the control procedure uses a mathematic model M, representing a kinetics of the solutes in a distribution volume in the patient, in order to determine a value of an equivalent sodium concentration Na eq(t) at the control instant t, the model being memorised in a memory associated to the control unit, the control unit being configured such as to apply the following values in input to the mathematical model:
  • the estimated total convective and diffusive clearance value Cl mes(t) is calculated on the basis of a current measured value of the infusion rate Q INFmes(t) and of one from between a current measured value of blood flow Q Bmes(t) and a current diffusive clearance value Cl diff(t) .
  • the estimated total convective and diffusive clearance value Cl mes(t) can be mathematically extrapolated from preceding assumed values from C1.
  • the mathematical model is representative of a kinetics of the solutes in a distribution volume in the patient, optionally according to a single-compartment model.
  • control procedure comprises also using the equivalent sodium concentration value at the instant t (i.e. Na eq(t) ) for the determination of the control values.
  • control procedure comprises the following sub-steps:
  • control procedure comprises the sub-steps of:
  • control conductivity or sodium concentration Cd (t) , Na (t) to be imposed on the liquid crossing the dialysis line and/or the infusion line is calculated as a function of the second error parameter ERR_BV_Na (t) and a function of the value of conductivity or sodium concentration Cd (t- ⁇ t) , Na (t- ⁇ t) relating to the preceding control instant.
  • control flow value to be imposed on the weight loss WLR (t) is calculated a function of the error parameter ERR_BV_UF (t) and a function of the ultrafiltration flow rate value UFR (t- ⁇ t) relating to the preceding control instant.
  • control unit is configured for:
  • commanding the infusion of the bolus comprises imposing a predetermined flow rate on the infusion pump for a predetermined administration time.
  • control unit is configured such as to impose, during the administration of the bolus, an ultrafiltration flow rate of zero.
  • commanding the bolus comprises commanding, during administration of the bolus, the second regulating device of the liquid composition such as to impose a predetermined value on the conductivity or sodium concentration Cd (t) , Na (t) in the liquid crossing the infusion line.
  • the sensor means comprise at least one first sensor S 7 active on the extracorporeal circuit for detecting the variation BV % of the blood volume of the patient.
  • the sensor means comprise at least one second sensor S 6 active on the evacuation line for determining the ultrafiltration flow rate UFR across the membrane, or the weight loss rate WLR of the patient, or a accumulated weight loss WL.
  • the sensor means comprise at least one third sensor S 8 active on the dialysis line or on the infusion line or on a common supply line of the dialysis line and the infusion line, the third sensor being a conductivity or concentration sensor predisposed for determining the conductivity of a liquid crossing the dialysis line and/or the infusion line or the sodium concentration of the liquid crossing the dialysis line and/or the infusion line.
  • the sensor means comprise at least one fourth sensor S 5 for determining an infusion flow rate Q INF of the replacement fluid crossing the infusion line.
  • the sensor means comprise at least one fifth pressure sensor S 1 , S 2 , S 3 , S 4 for determining a transmembrane pressure TMP between the first and the second chamber.
  • An 85 th aspect comprises a control unit configured or programmed to perform the control procedure and/or the setting sequence of one of the preceding aspects.
  • the control unit can be of an analog or digital type (for example a CPU with one or more processors) or a combination of analog and digital units.
  • An 86 th aspect comprises a data support for storing instructions which, when performed by a control unit of an apparatus for blood treatment, determine the carrying-out on the apparatus of a control procedure and/or a setting sequence according to any one of the preceding aspects.
  • the data support can comprise a mass memory, for example optical or magnetic, an electromagnetic signal, a re-programmable memory (EPROM, FLASH) or a memory of another nature.
  • An 87 th aspect according to the preceding aspect provides that the setting sequence and the control procedure be contemporaneously performed on the blood treatment apparatus, the setting sequence and control procedure comprising the respective steps described in any one of aspects from the 30 th to the 80 th .
  • An 88 th aspect comprises a method performed using an apparatus for blood treatment of the type of the 1 st or of the 2 nd aspect, the method comprising executing a control procedure and/or a setting sequence according to any one of the preceding aspects.
  • a method of extracorporeal blood treatment executed using an apparatus which comprises: at least one treatment unit, having at least one first chamber and at least one second chamber, separated from one another by a semipermeable membrane, at least one blood removal line connected to an inlet port of the first chamber and predisposed to remove blood from a patient, at least one blood return line connected with an outlet port of the first chamber and predisposed to return treated blood to the patient (the blood removal line, the blood return line and the first chamber being part of an extracorporeal blood circuit), at least one infusion line of a replacement fluid connected with the extracorporeal circuit or directly connectable with a patient and, optionally, a dialysis line connected in inlet to the second chamber, at least one fluid evacuation line connected to an outlet port of the second chamber, and sensor means.
  • the sensor means are positioned and configured such as to determine:
  • the method comprises performing a control procedure comprising:
  • the control procedure may include the respective steps disclosed in any one of aspects from 2 nd to 29 th .
  • a method of extracorporeal blood treatment executed using an apparatus which comprises:
  • At least one treatment unit having at least one first chamber and at least one second chamber, separated from one another by a semipermeable membrane, at least one blood removal line connected to an inlet port of the first chamber and predisposed to remove blood from a patient,
  • the blood return line connected to an outlet port of the first chamber and predisposed to return treated blood to the patient (the blood removal line, the blood return line and the first chamber being part of an extracorporeal blood circuit), at least one infusion line of a replacement fluid connected to the extracorporeal circuit or directly connectable with a patient and, optionally, a dialysis line connected in inlet to the second chamber, at least one fluid evacuation line connected with an outlet port of the second chamber, and sensor means.
  • the sensor means are positioned and configured such as to determine:
  • control procedure comprising:
  • the control procedure may include the respective steps disclosed in any one of aspects from 2 nd to 29 th .
  • a 92 nd aspect concerns a method of extracorporeal blood treatment using an apparatus comprising at least one treatment unit having at least one first chamber and at least one second chamber separated from one another by a semipermeable membrane; at least one blood removal line connected to an inlet port of the first chamber and predisposed for removing blood from a patient; at least one blood return line connected with an outlet port of the first chamber and predisposed to return treated blood to the patient.
  • the blood removal line, the blood return line and the first chamber are part of an extracorporeal blood circuit of the apparatus.
  • the apparatus also exhibits:
  • the apparatus comprises a first regulating device active on at least one of the extracorporeal circuit and the fluid evacuation line and configured such as to regulate an ultrafiltration flow rate UFR or a transmembrane pressure TMP between the first and the second chamber of the treatment unit, wherein the method comprises performing a control procedure in order to regulate the weight loss rate and at least one setting sequence for maximising the convective exchange across the semipermeable membrane.
  • control procedure and the setting sequence may include the respective steps disclosed in any one of aspects from 31 st to 84 th .
  • FIG. 1 is a schematic illustration of a first example of a blood treatment apparatus of the invention
  • FIG. 2 is a schematic view of a second example of a blood treatment apparatus of the invention.
  • FIG. 3 is a block diagram relating to the periodic calculation by means of a mathematical model M of flow rate control values relating to weight loss and concentration/conductivity imposed on the apparatus;
  • FIG. 4 is a flow diagram showing a control procedure according to an aspect of the invention, which can be carried out by the control unit of an apparatus, for example, of the type illustrated in FIG. 1 or FIG. 2 ;
  • FIG. 5 is a flow chart showing a setting sequence according to an aspect of the invention, which can be carried out by the control unit of an apparatus for example of the type illustrated in FIG. 1 and FIG. 2 , during performance of the control procedure of FIG. 4 ;
  • FIG. 6 is a time chart showing the progression of the transmembrane pressure TMP during a setting sequence of the TMP, in an aspect of the invention
  • FIG. 7 is a time chart showing the progression of the transmembrane pressure TMP during a further setting sequence of the TMP, in an aspect of the invention.
  • FIG. 8 is a time chart relating to a plurality of successive TMP setting sequences, in an aspect of the invention.
  • FIG. 9 is a time chart relating to a plurality of TMP setting sequences, in the presence of setting variations in the blood flow rate
  • FIGS. 10 and 11 comparatively illustrated the progression of the plasmatic conductivity measure experimentally on a patient and the progression of the estimated plasma conductivity using the mathematical model M in accordance with aspects of the invention
  • FIGS. 12 and 13 show the progression of the set value of the TMP determined by the setting sequence respectively in the case of constant weight loss rate and in the case of varied weight loss rate during a same setting sequence, for example on the action of the control procedure in accordance with aspects of the invention.
  • FIG. 14 shows the system constituted by the patient and the treatment unit to which reference is made in determining the mathematical model M in accordance with aspects of the invention.
  • the apparatus 1 denotes in its entirety an apparatus for extracorporeal blood treatment.
  • the apparatus 1 comprises at least one treatment unit 2 , for example a hemofilter, a hemodiafilter, a plasma filter, having at least one first chamber 3 and at least one second chamber 4 separated from one another by a semipermeable membrane 5 .
  • a blood removal line 6 is connected with an inlet port of the first chamber 3 and is predisposed, in operating conditions of connection to a patient, to remove blood from a vascular access V 1 inserted for example in a fistula F of the patient.
  • a blood return line 7 connected to an outlet port of the first chamber is predisposed to receive the treated blood from the treatment unit and to return the treated blood to a further vascular access V 2 connected with the patient's fistula.
  • the configuration of the vascular access can be of any nature: for example a catheter, a port implanted in the patient, a cannula, a needle, etc.
  • the blood removal line 6 , the first chamber 3 of the treatment unit and the blood return line 7 to the patient in practice are part of an extracorporeal blood circuit 8 which, during the use of the apparatus 1 , provides for the circulation of the blood externally of the patient's body when subjected to treatment.
  • an infusion line 9 of a replacement fluid is connected to the blood removal line 6 , upstream of the first chamber 3 .
  • the infusion line 9 might be connected to the return line 7 , downstream of the first chamber 3 .
  • an infusion line 9 a is connected downstream while an infusion line 9 b is connected upstream of the unit 2 .
  • infusion lines can also be provided, for example connected downstream and/or upstream of the treatment unit.
  • the apparatus 1 further comprises at least one fluid evacuation line 10 connected with an outlet port of the second chamber 4 for receiving at least a fluid filtered across the semipermeable membrane.
  • a dialysis line 11 for supplying a fresh treatment fluid in inlet to the second chamber 4 : the presence of this line is not strictly necessary, as in the absence of the line 11 the apparatus is in any case able to perform treatments such as hemofiltration or plasma filtration.
  • a fluid check organ 12 can be used to selectively enable or inhibit a passage of fluid across the dialysis line 11 , according to whether it is desired, or not, to have a purification by diffusive effect internally of the treatment unit.
  • the apparatus 1 comprises sensor means (S 1 , S 2 , S 3 , S 4 , S 5 , S 6 , S 7 , S 8 , S 9 , S 10 ) for determining the values assumed during treatment by the parameters described herein below. There follows a description of sensor means for each of the main parameters to be read. The described sensor means can be present both in the apparatus of FIG. 1 and in the apparatus of FIG. 2 .
  • TMP Transmembrane Pressure
  • transmembrane pressure which is defined as the mean pressure applied on the side of the first chamber towards the side of the second chamber.
  • TMP transmembrane pressure
  • TMP Ps + Pv 2 - Pi + Po 2
  • the apparatus can comprise a sensor S 5 of infusion flow rate Q INF of the replacement fluid crossing the infusion line 9 or the infusion lines 9 a , 9 b .
  • the sensor or sensors S 5 for detecting the flow can in practice be volumetric sensors, mass sensors such as for example Coriolis sensors, weight sensors such as for example scales, pump revolution sensors or sensors of still other types: as the type of sensors usable is not significant and since the techniques and the sensors for detecting absolute or differential flow values are known and within the experience of the expert person in the field, no further details thereof are included in the present text.
  • the infusion flow rate sensors comprise sensors S 5 destined to determine the number of revolutions of the infusion pumps, by sending a corresponding signal to the control unit 15 which is configured such as to calculate a flow rate along the respective infusion line.
  • the apparatus 1 can further comprise at least one sensor S 6 for detecting the ultrafiltration flow rate across the semipermeable membrane 5 .
  • a flow sensor S 6 can be comprised on the evacuation line 10 and a flow sensor S 6 on the dialysis line such as to provide the control unit 15 with the instant value of the respective flows and thus enable the control unit to calculate an instant ultrafiltration flow.
  • a differential sensor can be provided, active on the evacuation line and dialysis line and therefore able directly to provide a signal relating to the ultrafiltration flow rate.
  • the sensor or sensors S 6 can in practice be volumetric sensors, mass sensors such as for example Coriolis sensors, weight sensors such as for example scales, pump revolution sensors, or sensors of yet another type: as the type of sensors usable is not significant and since the techniques and the sensors for detecting absolute or differential flow values are known and within the experience of the expert person in the field, no further details thereof are included in the present text.
  • the control unit 15 can be programmed to derive the weight loss rate WLR.
  • a sensor can be provided which is able directly to provide a signal which gives the weight loss rate: for example a sensor able to differentially measure the rate taken from the evacuation line and to subtract the flow rate crossing the dialysis line and/or the rate or rates of infusion.
  • the sensor can materially be a mass flow sensor (for example a Coriolis sensor), volumetric, electromagnetic, ponderal (such as a scales able to weigh bags of fluid) or another type.
  • the apparatus 1 comprises a sensor S 7 for variation of blood volume (BV %) or a parameter from which the variation in blood volume can be calculated in relation to the blood of a patient subjected to treatment.
  • the blood volume variation sensor can for example be optical, able to detect a variation in the optical properties of the blood crossing a calibrated portion of tube.
  • HGB 0 represents the concentration of hemoglobin at start of treatment and HGB t the concentration of hemoglobin at time t in which BV % is calculated.
  • the hemoglobin concentration is calculated based on the variation of optic absorbance, at a predetermined wavelength, of the blood flowing in the blood removal line 6 , across a tract of tube having the appropriate optical properties, precedingly characterised.
  • the apparatus 1 can also determine the weight loss over a time period, for example from start of treatment up to a certain instant t: for example the control unit 15 can be programmed to integrate the weight loss rate WLR over the time.
  • a weight loss sensor can be provided, for example a sensor destined to detect the variation in overall weight of a patient during treatment, or a sensor destined to directly detect the overall weight of the net fluid extracted from a patient.
  • the apparatus 1 further comprises at least one sensor S 8 of conductivity or sodium concentration (or another substance that is to be monitored) of the liquid crossing the dialysis line and/or the infusion line.
  • the conductivity or concentration sensor S 8 can be located immediately downstream of a device for regulating a composition of dialysis liquid and/or replacement liquid, which will be more fully described in the following.
  • the apparatus 1 further comprises a first regulating device 20 for regulating ultrafiltration or transmembrane pressure TMP between the first and the second chamber of the treatment unit.
  • the first regulating device 20 is connected to the control unit 15 and active on at least one of the extracorporeal circuit 8 and the fluid evacuation line 10 .
  • the first regulating device can comprise for example: a pump 13 located on the fluid evacuation line 10 , or two pumps piloted differentially such as two blood pumps located one upstream and one downstream of the filter unit, or a plurality of pumps located on the lines and piloted such as to create an ultrafiltration flow across the membrane, or combinations of one or more pumps and valves appropriately arranged on the blood line or fluid evacuation line, or others besides.
  • the device 20 comprises an ultrafiltration pump 13 operating on the evacuation line and able to recall fluid from the second chamber.
  • a treatment fluid supply pump 14 is comprised: in this case the regulating device 20 therefore comprises both the ultrafiltration pump and the supply pump, which are appropriately piloted differentially such as to create an ultrafiltration flow UFR across the membrane.
  • the control unit 15 for example of analog type or a microprocessor, connected with the regulating device, is configured such as to pilot the above-described pumps.
  • control unit can operate such as to pilot the device 20 (in the example of FIGS. 1 and 2 , the pump or pumps 13 and 14 ) such that the TMP measured value corresponds to the set value for the TMP.
  • control unit acts continuously or periodically on the first regulating device 20 such that, instant by instant, the TMP measured corresponds to the value set at that instant (TMP pressure control).
  • TMP pressure control the ultrafiltration flow rate UFR across the membrane and thus the quantity of fluid removed from the blood present in the first chamber is a function of the TMP imposed.
  • control unit 15 can be programmed such that the ultrafiltration flow rate UFR follows one or more set values for ultrafiltration flow rate (volumetric control): in this case, the TMP will be variable and the control unit will act such as to maintain the ultrafiltration flow rate constantly close to or equal to the reference value or values predicted or calculated for the UFR.
  • volumetric control volumetric control
  • the Second Regulating Device The Second Regulating Device.
  • the apparatus 1 further comprises a second regulating device 30 for regulating a composition of the dialysis liquid and/or the replacement liquid.
  • the device 30 comprises one, two or more containers of concentrate 31 , 32 , 33 located on respective injection lines 31 a , 32 a , 33 a which are predisposed to supply substances such as electrolytes, buffer agents or others towards a preparation line 35 of the liquid located upstream of the dialysis line 11 .
  • the concentrate containers can comprise concentrates in the liquid state or solid state, for example powder.
  • Injection pumps 31 b , 32 b , 33 b can be present on the injection lines to move the fluid along the respective injection line towards the preparation line 35 which collects the liquid, for example water, from a source 36 .
  • the source 36 can comprise a water tap or a source of ultra-pure liquid or another besides: the water collected from the source and possibly subjected to filtering stages 36 a (not detailed as known and not relevant to the present invention) is provided with the necessary substances by the device 30 .
  • the concentration or conductivity sensor S 8 is able to provide the control unit 15 with a relative signal to conductivity or concentration of a predetermined substance (for example sodium) of the fluid crossing the line 35 such that the control unit can act on the second regulating device 30 and in particular on the pumps 31 b , 32 b , 33 b in order to regulate the conductivity Cd or concentration, for example of sodium [Na], of the liquid crossing the dialysis line.
  • a predetermined substance for example sodium
  • the infusion line 9 collects the fluid from a source 37 (for example a bag containing replacement fluid) independent with respect to the source 36 , while the preparation line 35 exclusively supplies the supply line 11 of the dialysis liquid.
  • both the infusion lines 9 a and 9 b , as well as the dialysis liquid supply line collect fluid from the supply line 35 , such that the conductivity or the concentration of the dialysis fluid crossing the line 11 and the fluid crossing the infusion line 9 a , 9 b is the same.
  • the control unit 15 can comprise one or more digital units, for example microprocessors, or one or more analog units, or a special combination of digital and analog units.
  • the control unit is connected with the first and the second regulating devices 20 , 30 , with a user interface 22 , with the sensor means and with the various actuator organs (blood pump 21 , infusion pump 16 , 16 a , 16 b , ultrafiltration pump 13 , valve 12 ) located along the lines 7 , 8 , 9 , 9 a , 9 b , 10 , 11 and is configured or programmed to perform the procedures described herein.
  • the control unit is programmable
  • the unit is connected with a data support 15 a for storing instructions which, when performed by the control unit, determine performing of the procedures which will be described herein below.
  • the data support can comprise a mass data memory, for example optical or magnetic, a re-programmable memory (EPROM, FLASH) or a memory of another nature.
  • control unit 15 is programmed or configured such as to perform, on control instants t temporally one after another (for example the instants t can be temporally equidistant), a control procedure 50 comprising the steps described herein below.
  • control unit can be programmed to perform, in agreement with the control procedure, also a TMP setting sequence: the setting sequence of the TMP and the control procedure are coordinated by the control unit such as to prevent negative interactions.
  • the control procedure comprises receiving, for example via the interface 22 , prescription values of the blood volume variation BV % target , of the weight loss WL target , the plasma conductivity or sodium concentration C target , Na target , the volume of infusion V INFtarget to be achieved in the patient in a predetermined treatment time T.
  • the user interface can enable entering of the prescription values and the selection of a treatment time in which the prescription values have to be achieved.
  • the control unit can be programmed to receive prescription values of the blood volume variation BV % target , the weight loss WL target , the plasma conductivity or sodium concentration C target , Na target , to be reached in the patient in a predetermined treatment time, as well as a transmembrane pressure value TMP target to be pursued during the treatment with the aim of maximising the convective exchange; this last value is in reality calculated by the setting sequence described herein below.
  • the control procedure having received the prescription values of the blood volume variation BV % target , the weight loss WL target to be achieved at end of treatment and having received a treatment time value T, comprises determining, on the basis of the prescription values and the treatment time value T, respective target profiles which describe the desired progression over time of the variation of blood volume BV % target(t) , and weight loss WL target(t) (or the weight loss rate WLR target(t) .
  • the target profile which is to describe the conductivity or sodium concentration of the dialysis or infusion liquid. This operation is done in two different ways depending on whether the apparatus 1 is provided or not with a conductivity or concentration sensor directly active on the patient and able to provide the conductivity or sodium concentration.
  • step 101 is used for determining an target profile which described the desired progression over time of the conductivity or sodium concentration C target(t) , Na target(t) that the blood must following during the treatment.
  • the apparatus 1 does not comprise a conductivity or concentration sensor directly active on the patient or the extracorporeal blood circuit, during stage 101 the procedure generates an target profile which describes the desired progression over time of the equivalent sodium concentration Nq eq-target(t) : in practice the control unit 15 is programmed or configured such that during the treatment the control procedure iteratively determines the equivalent sodium concentration Na eq(t) on the basis of a mathematical model M and compares the equivalent sodium concentration Na eq(t) with the respective target profile.
  • the control procedure comprises receiving, from the sensor means, measured values of blood volume BV % mes , of the ultrafiltration flow rate or weight loss rate UFR mes , WLR mes (or alternatively accumulated weight loss WL mes ), of the conductivity or sodium concentration in the liquid crossing the dialysis line and/or the infusion line Cd mes ; Na mes and the infusion flow rate Q INFmes .
  • the control unit can also receive a measured value of the transmembrane pressure TMP mes .
  • the control procedure also comprises calculating, in accordance with the measured values and the prescription values of the blood volume variation BV % target , the weight loss WL target , the plasma conductivity or sodium concentration C target , Na target , the infusion volume V INFtarget to be reached in the patient in a predetermined treatment time, the following control values to impose during a time interval after the control instant.
  • control values that are determined comprise:
  • control unit is able to receive the measured values and the respective prescription values and to generate values that are then used to regulate the composition of the dialysis and/or infusion values, the weight loss rate and the infusion flow rate, thus realising a system able to guarantee a high degree of comfort for the patient and a predefined convective exchange (that is, the infusion rate under carefully controlled conditions).
  • control procedure comprises calculating the following control values to be imposed during a time interval following the control instant based on: the measured values of the blood volume variation BV % mes , the ultrafiltration flow rate UFR mes or the weight loss rate WLR mes (or alternatively the accumulated weight loss WL mes ), the conductivity or sodium concentration of the liquid crossing the dialysis line and/or the infusion line Cd mes , Na mes and the transmembrane pressure TMP mes , and the prescription values of the blood volume variation BV % target , the weight loss WL target , the plasma conductivity or sodium concentration C target , Na target , to be achieved in the patient over a predetermined treatment time and the transmembrane pressure TMP target to be observed during the treatment.
  • control values that are determined comprise:
  • control unit is able to receive the above-mentioned measured values and the respective prescription values and to generate values that are then used to regulate the composition of the dialysis liquid and/or the infusion liquid, the weight loss rate and the TMP, thus realising a system able to guarantee a high degree of comfort for the patient and an optimum convective exchange (the TMP being controllable for example in order to maximise the convective exchange).
  • control values are imposed during a time interval ⁇ t following the control instant t (step 103 ).
  • control value relating to the conductivity or sodium concentration Cd (t) ; Na (t) is imposed by the control unit 15 commanding the second regulating device 30
  • control values relating to the weight loss rate WLR (t) and the infusion flow rate Q INF(t) are imposed by the control unit by acting on the first regulating device 20 and on the pump 16 or pumps 16 a , 16 b .
  • the control values relating to the weight loss rate WLR (t) and the transmembrane pressure TMP (t) are imposed by the control unit once more by acting appropriately on the first regulating device 20 and the pump 16 or pumps 16 a , 16 b .
  • the control unit commands the second regulating device 30 and thanks to the above-described hydraulic configuration imposes the same conductivity or sodium concentration on both the dialysis liquid and the infusion liquid or liquids.
  • the apparatus 1 can also not exhibit a conductivity or concentration sensor directly acting on the patient or on the extracorporeal blood circuit.
  • the control procedure uses a mathematical model M representing a kinetics of solutes in a distribution volume V in the patient for iteratively calculating, at each control instant t, an equivalent sodium concentration value Na eq(t) .
  • the model M can for example be memorised in the memory 15 a associated to the control unit which is configured to acquire (step 102 a ) and apply the following values in inlet to the mathematical model:
  • mathematic model M is now illustrated, with reference to the system constituted by the patient and the treatment unit illustrated in FIG. 14 .
  • J diff Mass flow of sodium across the membrane due to the diffusive process
  • J conv Mass flow of sodium across the membrane due to the convective process
  • Na B Plasma sodium concentration
  • WLR Weight loss rate
  • V Sodium distribution volume in the patient.
  • the mass balance equation for the system can be represented as (see the system of FIG. 14 ):
  • TBW estimated volume of corporeal water (see below for some of the estimation methods for TWB);
  • WL target prescription value of weight loss
  • WL(t) weight loss achieved at time t.
  • Equation (2) From equation (2) the following equation system can be derived, obtained by considering the various infusion flow rate values applied during the treatment (Q INF1 , Q INF2 . . . Q INFn ):
  • Each equation can be resolved by integration on the corresponding time interval.
  • the control procedure enables (step 102 b ) the value of an equivalent sodium concentration Na eq(t) to be obtained at the control instant t which is then related to a respective target value for the equivalent conductivity or sodium concentration C eq-target , Na eq-target and used for determining the above-described control values at the control instant (step 102 ).
  • the mathematical model M is representative of a kinetics of the solutes in a distribution volume in the patient V according to a single-compartment model.
  • the distribution volume V is determined for each patient on the basis of the weight loss objective WL target , the total accumulated weight loss WL (t) and the volume of corporeal water TBW estimated for example on the basis of information such as age, sex, height and weight of the patient.
  • some example formulae for calculating the volume of corporeal water TBW are the following:
  • Input parameters Sex, Height [cm], Weight [Kg], Age [years], Volume %
  • the control procedure imposes a variable concentration or conductivity on the dialysis liquid and/or the infusion liquid; in this situation, the constant concentration of sodium in the dialysis liquid is defined as equivalent sodium concentration at instant t, which constant concentration, if applied from the start of the treatment up to a certain instant t would lead to a same plasma sodium concentration in the patient as that which is obtained at the same instant t with the sodium concentration variation or conductivity imposed by the control procedure up to the time t.
  • FIGS. 10 and 11 show a clear convergence between the plasma conductivity measured experimentally and the plasma conductivity calculated using the model M: this confirms the accuracy of the mathematical model used.
  • the control procedure comprises a further sub-step of calculating the error ( 102 d ) which comprises determining at least one first error parameter ERR_BV_UF (t) according to the difference between the measured value of the first parameter BV % mes at the control instant t and a corresponding value on the target profile relating to the variation in blood volume in the time BV % target(t) and the difference between a measured value of the weight loss WL mes (or the weight loss rate WLR mes ) at the control instant t and a corresponding value given by the target profile relating to the weight loss WL target(t) (or respectively the weight loss rate WLR target(t) ) in the time.
  • the stage of calculating the error also comprises determining at least one second error parameter ERR_BV_Na (t) as a function of the difference between the equivalent sodium concentration value Na eq(t) at the control instant t and a corresponding value on the target profile relating to the variation over the time of the equivalent sodium concentration Na eq-target(t) , and the difference between the measured value of the first parameter BV % mes at the control instant t and the corresponding value on the target profile in relation to the variation in blood volume in the time BV % target(t) .
  • the control procedure performed by the unit 15 comprises calculating (sub-step 102 f ) the control value of conductivity or sodium concentration Cd (t) , Na (t) to be imposed in the liquid crossing the dialysis line and/or the infusion line according to the second error parameter ERR_BV_Na (t) and the conductivity or sodium concentration value Cd (t- ⁇ t) , Na (t- ⁇ t) relating to the preceding control instant and previously acquired (sub-step 102 e ).
  • control procedure performed by the unit 15 comprises calculating (sub-step 102 f ) the control value to be set on the weight loss rate WLR (t) which is calculated according to the first error parameter ERR_BV_UF (t) and according to the ultrafiltration flow rate UFR (t- ⁇ t) relative to the preceding control instant.
  • a step of verification can be included in which it is verified that the control values are within predetermined bands; a step of adjusting the control values themselves (step 104 ), if required, is also included.
  • the control procedure can comprise a stage of verification and alarm 105 comprising verifying whether the measured values of the first parameter BV % mes(t) , the second parameter UFR mes(t) , WLR mes(t) , WL mes(t) , the third parameter Cd mes(t) , Na mes(t) , and/or the equivalent concentration Na eq(t) exceed or not the respective safety threshold values.
  • control procedure can include a compensation sequence (step 106 ) which comprises comparing the measured values of the first parameter BV % mes(t) with a reference threshold and verifying whether the measured value of the first parameter falls below the threshold and commanding infusion of a bolus of predetermined replacement liquid volume into the infusion line if the verification gives a positive outcome.
  • the bolus infusion can be done by imposing a predetermined rate over a predetermined administration time on the infusion pump and appropriately commanding the second regulating device 30 , for example in such a way as to increase the sodium concentration in the infusion liquid for a brief time interval.
  • the control procedure can comprise imposing an ultrafiltration flow rate UFR of zero.
  • control unit can be programmed also to perform, in addition to the control procedure as described above, a setting sequence 200 (see FIG. 5 ) of the transmembrane pressure TMP.
  • This type of sequence is performed if it is intended to control the apparatus also on the basis of the TMP and for example to maximise as much as possible the infused fluid volume, thus increasing the convective exchange.
  • the setting sequence is performed at a setting instant indicated by T and possibly repeated a plurality of times during a treatment. For example the setting sequence can be performed while the control procedure is contemporaneously performed.
  • control unit is configured to repeat both the control procedure (at a plurality of control instants t that are temporally consecutive to one another) and the control procedure of the TMP (at a plurality of control instants t that are temporally consecutive to one another).
  • control unit is configured to impose the control value or values determined using the control procedure during a time interval ⁇ t following each control instant t, cyclically repeating the control procedure during the whole treatment.
  • control unit is also configured to perform the setting sequence at a plurality of setting instants ⁇ temporally consecutive to one another, imposing the TMP thus determined.
  • the control unit is configured to perform the control procedure at more frequent control instants with respect to the setting instants in which the setting sequence is performed.
  • the sequence comprises the following steps, aimed at identifying an optimal value of TMP at which a maximisation of the ultrafiltration is obtained.
  • the sequence comprises, for example by acting on the pump 13 of the first regulating pump 20 , determining a first increase ⁇ TMP n (step 201 ) to reach a second transmembrane pressure value TMP n+1 ; then the sequence comprises measuring or calculating (step 202 ) a variation ⁇ UFR (n) between the ultrafiltration flow UFR across the membrane 5 at the first transmembrane pressure TMP n and the ultrafiltration flow UFR at the second transmembrane pressure TMP n+1 : the variation of the ultrafiltration flow is determined either by direct measuring of the ultrafiltration flow or indirectly by taking account of both the flow variations of the replacement liquid ⁇ Q INF(n) along the infusion line and the variations of weight loss rate ⁇ WLR (n) due to the control procedure.
  • control sequence comprises comparing (step 203 ) the ultrafiltration variation ⁇ UFR (n) with a reference value and, if the variation value ⁇ UFR (n) is greater than the reference value, commanding the first regulating device 20 to impose a second increase ⁇ TMP n+1 on the transmembrane pressure in order to reach a third transmembrane pressure value TMP n+2 , and so on, cyclically repeating the described sequence for successive increases.
  • the ultrafiltration flow rate variation ⁇ UFR is compared at step 203 with a reference flow rate, for example 3 ml/min and, should the ultrafiltration flow rate be greater than 3 ml/min, the ultrafiltration pump 13 is commanded such as to set an increase of TMP that is greater than the preceding one.
  • a reference flow rate for example 3 ml/min
  • the ultrafiltration pump 13 is commanded such as to set an increase of TMP that is greater than the preceding one.
  • control unit can considerably increase the amplitude of the following pressure increase, in this way accelerating the search for and the setting of the optimal TMP. If on the other hand the value of the variation ⁇ UFR of the ultrafiltration flow (step 203 ) is lower than the reference value, the TMP setting procedure is interrupted, as will be more fully described herein below, as the unit in this case considers that it has reach the optimal TMP and thus maintains it as the set value (step 204 ).
  • FIG. 6 shows a system of Cartesian axes in which the x-axis represents the time and the y-axis the TMP pressure the pressure TMP set instant by instant:
  • FIG. 6 shows an embodiment of a sequence of TMP setting that can be performed by a control unit which is part of the apparatus 1 of the type illustrated in FIG. 1 or FIG. 2 .
  • a TMP setting sequence is started by the control unit.
  • the control unit maintains the TMP at a value of TMP 1 for a first time interval t 1 -t 2 .
  • a pressure increase of 20 mmHg is imposed on the set TMP value, passing to a set value of TMP 2 , with a consequent activation of the ultrafiltration pump 13 and the infusion pump 16 (or at least one of the pumps 16 a , 16 b in the case of FIG. 2 ).
  • the variation in ultrafiltration flow rate ⁇ UFR is greater than 3 ml/min, for example 12 ml/min
  • the successive increase in the set value of TMP is optionally imposed at greater than 20 mmHg and, in the illustrated example, at 60 mmHg.
  • control unit In response to the new set value of TMP, i.e. TMP 3 , the control unit also commands the acceleration of the infusion pump such as to balance the effect of the greater ultrafiltration.
  • the duration of the interval t 3 -t 4 is not necessary equal to that of the interval t 2 -t 3 : for example the unit 15 can be configured to impose a variable interval, which becomes greater as a function with the increment in TMP that precedes it, with the aim of enabling a transitory of adaptation for the ultrafiltration pump and the infusion pump or pumps.
  • a new TMP increase is imposed, 20 mmHg, and after a further interval T (in FIG. 6 : t 4 -t 5 ), the increase in the ultrafiltration flow is verified. If, as in the illustrated case, the variation in flow rate ⁇ UFR is less than 3 ml/min, the setting sequence is considered to be concluded (“END” in FIG. 6 ) and the final TMP value reached (i.e. TMP 4 in FIG. 6 ) is imposed as set value. Otherwise, a new TMP increase is imposed, which can be again of 20 mmHg or can be a function of the variation measured ⁇ UFR in ultrafiltration flow UFR.
  • FIG. 7 illustrates a situation in which the above-described steps are repeated up to reaching pressure TMP 3 ; thereafter, the setting sequence can comprise the TMP variation in one or two steps of predetermined entity with the aim of enabling stabilisation of the control system.
  • the TMP variation or variations are kept lower than or equal to a relatively low value, for example 20 mmHg.
  • FIG. 7 shows a stabilising step, denotes by s.
  • the sequence repeats the previously-described steps with reference to intervals from t 2 to t 4 .
  • a pressure increment of 20 mmHg is imposed on the value of the TMP passing to a set value TMP 5 with a consequent activating of the ultrafiltration pump 13 and the infusion pump 16 (or at least one of the pumps 16 a , 16 b in the case of FIG. 2 ) such as to balance the effect of the greater ultrafiltration.
  • the variation ⁇ UFR in ultrafiltration flow rate UFR is above 3 ml/min, for example 12 ml/min
  • the successive increment of the TMP set value is imposed at greater than 20 mmHg and, in the illustrated example, at 60 mmHg.
  • the control unit In response to the new set value of TMP (TMP 6 ), the control unit also commands acceleration of the infusion pump such as to balance the effect of the greater ultrafiltration, according to one of the above-described control strategies. Then, a new TMP increase of 20 mmHg will be imposed and after a further interval T, the increase in the ultrafiltration flow rate ⁇ UFR will be verified. If in response the UFR varies by a value ⁇ UFR that is lower than 3 ml/min, the setting sequence is considered to be concluded. Otherwise, the described process is newly reiterated.
  • the sequence comprises that at the start of the setting sequence a TMP increase with a predetermined value is imposed, which can be the same or can vary during treatment, but is known a priori and is normally relatively small, for example 20 mmHg.
  • Increases after the first ( ⁇ TMP n+1 ) are either stabilising increases as described above, and therefore also of 20 mmHg or known and relatively small values, or TMP values calculated in accordance with the measured or estimated ultrafiltration variation value ⁇ UFR corresponding to the rise in immediately-preceding transmembrane pressure ( ⁇ TMP n ), or rises in TMP that are always constant and of known amplitude a priori.
  • control unit is configured such as to command the regulating device 20 , setting, as operating transmembrane pressure, the last pressure at which the value of the control parameter is less than the value of the respective reference value.
  • the setting sequence involves two actions. Firstly the variation in the ultrafiltration flow rate, if estimated as a function of the variation in the infusion rate, takes account of any variation in the weight loss rate, i.e. in each time interval t n -t n+1 (see FIGS. 6 and 7 for example) the variation ⁇ UFR is calculated as ⁇ Q INF + ⁇ WLR.
  • control unit 15 can be programmed such that during the setting sequence, following each command for increase of the transmembrane pressure, a time transitory T r is included (step 205 in FIG. 5 ) before performing a successive transmembrane pressure increase that is sufficiently long and generally of non-uniform duration.
  • the control unit 15 is further predisposed to verify (step 206 in FIG. 5 ) if between an increase in pressure and the next, there has been a variation in weight loss rate ⁇ WLR imposed by the control procedure and, if the response is affirmative, the duration of the time transitory T r is prolonged such that at least one predetermined auxiliary time delay (step 207 ), for example 50 seconds, passes from the previous variation in weight loss rate.
  • step 206 other verifications can also be made, such as a verification of any infusion stop and/or eventual flushing of one or more filter units which in any case would cause introduction of the auxiliary delay. Note that in all cases the auxiliary delay has a shorter duration than that of the period between a control procedure and a next.
  • control unit can also be predisposed to calculate the time transitory T r in accordance with the increase in pressure between a transmembrane pressure TMP n and a next TMP n+1 (prolonging T r in line if the TMP variation is greater) and/or as a function of the variation in weight loss rate ⁇ WLR imposed by the control procedure between a pressure increase and a next increase.
  • control unit 15 compares the value of the variation in ultrafiltration flow ⁇ UFR with a respect reference value ⁇ UFR ref only after the time transitory T r has passed, with the aim of enabling a stabilisation of the value of the ultrafiltration flow variation.
  • K is the relation between the value of the first transmembrane pressure increase ⁇ TMP 1 and a correction factor
  • ⁇ UFR 1 is the value for example of the variation in flow rate of the ultrafiltration pump 13 corresponding to the first increase in transmembrane pressure ⁇ TMP 1 .
  • ⁇ TMP 1 is predetermined and can be comprised between 10 and 30 mmHg (for example 20 mmHg).
  • the value of the correction factor can be determined in various ways: for example the value of the correction factor can be of a fixed amount and be greater than or equal to, preferably greater than, the reference parameter ⁇ UFR ref .
  • the control parameter value can be calculated as a function of ⁇ UFR ref and for example can be expressed by the function ⁇ UFR ref +1.
  • control unit is configured such as to verify that each pressure increase is less than a maximum safety value, for example 100 mmHg.
  • the maximum safety value could be programmable by the user or be set automatically by the control unit. In the last case the control unit can also be programmed to set a different maximum safety value in accordance with the type of treatment unit installed on the apparatus 1 .
  • the described sequence can be manually or automatically activated.
  • the apparatus 1 can comprise at least one user interface 22 , connected to the control unit and having at least one manual activating unit of the sequence.
  • the activation unit can comprise a part of the screen on which the user can act by pressure in order to initiate the TMP setting sequence and the control procedure.
  • the control unit is programmed to receive a start command of the sequence and/or of the procedure following the action exerted on the manual activation element. It is also possible to deactivate the setting sequence and/or the control procedure manually by acting on it or on a further element of the user interface 22 .
  • control unit 15 is programmed to automatically start the setting sequence and/or the control procedure.
  • control unit is programmed to cyclically repeat the control procedure, in brief intervals of for example one minute, and to automatically activate a first setting sequence after a brief time interval from the start of treatment.
  • the control unit can also be configured such as to measure a time that has passed since the end of the first sequence, and to automatically activate a second sequence after a second period of time has passed since the end of the first sequence.
  • a first setting sequence is activated after a time interval T 1 since start of treatment, the activation of a second setting sequence after a time interval T 2 after the end of the first sequence, and finally activating of a third sequence after a time interval T 3 following the end of the second sequence.
  • the type of requirement such as for example duration of the treatment, type of treatment unit, and more besides, it is possible to have a different number (two, three or more) of sequences during the treatment period.
  • control unit is also performing the control procedure 100 in parallel, such as to reach the desired objectives of weight loss and plasma sodium concentration in the patient without causing problems of hypovolemia.
  • the duration of the time intervals between consecutive sequences is optionally not uniform: for example the duration of each time interval following the first (T 2 , T 3 , . . . T n ) is greater than the duration of a time interval that precedes it.
  • the control unit can also be programmed to perform, following a setting sequence, a step of moderating the TMP setting value.
  • a step of moderating (denoted by A in FIG. 8 ) is included, which comprises lowering the TMP value determined thanks to the setting sequence by a predetermined amount ⁇ TMP with the aim of preventing the plateau zone of the TMP/UF curve from being reached.
  • FIG. 8 shows a succession of three setting sequences in which, following the third and final sequence, a reduction in TMP by a value ⁇ TMP is included, for example 20 mmHg.
  • the apparatus 1 comprises at least one blood pump 21 , operatively connected to the control unit 15 and operating at the removal line 6 or the return line 7 .
  • the blood pump can be a peristaltic pump.
  • the control unit 15 can also be programmed to detect a variation in the set value of the blood pump, which for example can be altered via the user interface 22 . Normally, the value of the blood pump is imposed at the start of treatment and maintained constant during treatment. If however the blood flow rate should be changed, the control unit 15 can be programmed to:
  • control unit 15 interrupts the sequence if a variation is verified that is greater for example than 50 ml/min: this is because the variation in the blood flow leads to a variation in TMP though the other operating conditions remain unaltered.
  • control unit can be programmed to:
  • control unit can be programmed to:
  • control unit 15 can be programmed to:
  • control unit can be programmed to:

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Urology & Nephrology (AREA)
  • Hematology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Emergency Medicine (AREA)
  • Cardiology (AREA)
  • External Artificial Organs (AREA)
  • Surgical Instruments (AREA)
US14/006,789 2011-03-21 2012-03-20 Apparatus for extracorporeal blood treatment Active 2033-02-09 US9199027B2 (en)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
ITMI2011A000441 2011-03-21
IT000441A ITMI20110441A1 (it) 2011-03-21 2011-03-21 Apparecchiatura per il trattamento extracorporeo di sangue.
ITM12011A0441 2011-03-21
PCT/IB2012/000534 WO2012172398A1 (fr) 2011-03-21 2012-03-20 Appareil pour traitement sanguin extracorporel

Publications (2)

Publication Number Publication Date
US20140088483A1 US20140088483A1 (en) 2014-03-27
US9199027B2 true US9199027B2 (en) 2015-12-01

Family

ID=43977107

Family Applications (1)

Application Number Title Priority Date Filing Date
US14/006,789 Active 2033-02-09 US9199027B2 (en) 2011-03-21 2012-03-20 Apparatus for extracorporeal blood treatment

Country Status (9)

Country Link
US (1) US9199027B2 (fr)
EP (1) EP2688601B1 (fr)
KR (1) KR101529414B1 (fr)
CN (1) CN103547300B (fr)
AU (1) AU2012270067B2 (fr)
CA (1) CA2830171A1 (fr)
ES (1) ES2547636T3 (fr)
IT (1) ITMI20110441A1 (fr)
WO (1) WO2012172398A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10342911B2 (en) * 2010-09-30 2019-07-09 Gambro Lundia Ab Apparatus for extracorporeal blood treatment
US10842924B2 (en) 2017-06-29 2020-11-24 Fresenius Medical Care Deutschland Gmbh Therapy control by comprehensive feedback
US10881347B2 (en) 2017-12-29 2021-01-05 Fresenius Medical Care Holdings, Inc. Closed loop dialysis treatment using adaptive ultrafiltration rates
US11383012B2 (en) 2016-11-25 2022-07-12 Gambro Lundia Ab Apparatus for extracorporeal blood treatment

Families Citing this family (65)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1850910A1 (fr) 2005-02-07 2007-11-07 Medtronic, Inc. Detecteur de desequilibre ionique
US9399091B2 (en) 2009-09-30 2016-07-26 Medtronic, Inc. System and method to regulate ultrafiltration
US9061099B2 (en) 2011-04-29 2015-06-23 Medtronic, Inc. Cardiovascular monitoring for fluid removal processes
US9456755B2 (en) 2011-04-29 2016-10-04 Medtronic, Inc. Method and device to monitor patients with kidney disease
US9848778B2 (en) 2011-04-29 2017-12-26 Medtronic, Inc. Method and device to monitor patients with kidney disease
EP3165245B1 (fr) 2011-08-02 2019-02-20 Medtronic, Inc. Système d'hémodialyse possédant un circuit de flux avec un volume à conformité régulée
US10857277B2 (en) 2011-08-16 2020-12-08 Medtronic, Inc. Modular hemodialysis system
US9713668B2 (en) 2012-01-04 2017-07-25 Medtronic, Inc. Multi-staged filtration system for blood fluid removal
US10905816B2 (en) 2012-12-10 2021-02-02 Medtronic, Inc. Sodium management system for hemodialysis
US9707328B2 (en) 2013-01-09 2017-07-18 Medtronic, Inc. Sorbent cartridge to measure solute concentrations
US9713666B2 (en) 2013-01-09 2017-07-25 Medtronic, Inc. Recirculating dialysate fluid circuit for blood measurement
US11154648B2 (en) 2013-01-09 2021-10-26 Medtronic, Inc. Fluid circuits for sorbent cartridge with sensors
US11565029B2 (en) 2013-01-09 2023-01-31 Medtronic, Inc. Sorbent cartridge with electrodes
US10010663B2 (en) 2013-02-01 2018-07-03 Medtronic, Inc. Fluid circuit for delivery of renal replacement therapies
US10850016B2 (en) 2013-02-01 2020-12-01 Medtronic, Inc. Modular fluid therapy system having jumpered flow paths and systems and methods for cleaning and disinfection
US9623164B2 (en) 2013-02-01 2017-04-18 Medtronic, Inc. Systems and methods for multifunctional volumetric fluid control
US9526822B2 (en) 2013-02-01 2016-12-27 Medtronic, Inc. Sodium and buffer source cartridges for use in a modular controlled compliant flow path
US10543052B2 (en) 2013-02-01 2020-01-28 Medtronic, Inc. Portable dialysis cabinet
US9144640B2 (en) 2013-02-02 2015-09-29 Medtronic, Inc. Sorbent cartridge configurations for improved dialysate regeneration
US9827361B2 (en) 2013-02-02 2017-11-28 Medtronic, Inc. pH buffer measurement system for hemodialysis systems
US10117985B2 (en) * 2013-08-21 2018-11-06 Fresenius Medical Care Holdings, Inc. Determining a volume of medical fluid pumped into or out of a medical fluid cassette
CN105848581B (zh) 2013-11-04 2019-01-01 美敦力公司 用于管理身体中的体液体积的方法和装置
US10537875B2 (en) 2013-11-26 2020-01-21 Medtronic, Inc. Precision recharging of sorbent materials using patient and session data
US9884145B2 (en) 2013-11-26 2018-02-06 Medtronic, Inc. Parallel modules for in-line recharging of sorbents using alternate duty cycles
CN105992552B (zh) 2013-11-27 2019-06-18 美敦力公司 精确透析监测及同步系统
WO2015199768A1 (fr) 2014-06-24 2015-12-30 Medtronic, Inc. Ensemble sorbant empilé
WO2015199766A1 (fr) 2014-06-24 2015-12-30 Medtronic, Inc. Ensemble de régénération de dialysat modulaire
DE102014012423A1 (de) * 2014-08-20 2016-02-25 Fresenius Medical Care Deutschland Gmbh Dialysemaschine mit der Fähigkeit zur Bestimmung einer prädialytischen Eigenschaft im Blut eines Dialysepatienten
DE102014013229A1 (de) * 2014-09-05 2016-03-10 Fresenius Medical Care Deutschland Gmbh Vorrichtung zur Durchführung einer Tidal-Peritonealdialysebehandlung
EP3010193B1 (fr) * 2014-10-17 2019-05-22 Gambro Lundia AB Procédé pour établir une communication sans fil entre un dispositif médical de traitement de fluide et un accessoire médical, ledit dispositif médical de traitement de fluide, système le comprenant et accessoire médical configuré pour établir une communication sans fil
US10874787B2 (en) 2014-12-10 2020-12-29 Medtronic, Inc. Degassing system for dialysis
US10098993B2 (en) 2014-12-10 2018-10-16 Medtronic, Inc. Sensing and storage system for fluid balance
US9895479B2 (en) 2014-12-10 2018-02-20 Medtronic, Inc. Water management system for use in dialysis
US9713665B2 (en) 2014-12-10 2017-07-25 Medtronic, Inc. Degassing system for dialysis
US10688233B2 (en) 2014-12-19 2020-06-23 Fenwal, Inc. Method and system for the automated processing of biological fluid during low level alert condition
DE102015005142A1 (de) * 2015-04-22 2016-10-27 Fresenius Medical Care Deutschland Gmbh Verfahren und Vorrichtung zur Herstellung einer medizinischen Lösung
US10335534B2 (en) 2015-11-06 2019-07-02 Medtronic, Inc. Dialysis prescription optimization for decreased arrhythmias
EP3865160B1 (fr) * 2015-11-09 2024-09-18 Gambro Lundia AB Appareil pour traitement sanguin extracorporel
US10994064B2 (en) 2016-08-10 2021-05-04 Medtronic, Inc. Peritoneal dialysate flow path sensing
US10874790B2 (en) 2016-08-10 2020-12-29 Medtronic, Inc. Peritoneal dialysis intracycle osmotic agent adjustment
US11013843B2 (en) 2016-09-09 2021-05-25 Medtronic, Inc. Peritoneal dialysis fluid testing system
WO2018095694A1 (fr) 2016-11-25 2018-05-31 Gambro Lundia Ab Appareil de traitement sanguin extracorporel
WO2018095691A1 (fr) * 2016-11-25 2018-05-31 Gambro Lundia Ab Appareil de traitement sanguin extracorporel
US10981148B2 (en) 2016-11-29 2021-04-20 Medtronic, Inc. Zirconium oxide module conditioning
DE102017210134A1 (de) * 2016-12-15 2018-06-21 Fresenius Medical Care Deutschland Gmbh System zur extrakorporalen Blutbehandlung, Behandlungsvorrichtung, Kit und Verfahren zum Betreiben eines Systems zur extrakorporalen Blutbehandlung
US11167068B2 (en) 2016-12-22 2021-11-09 Gambro Lundia Ab Apparatus for extracorporeal blood treatment
ES2937293T3 (es) 2016-12-22 2023-03-27 Gambro Lundia Ab Aparato para el tratamiento de sangre extracorpóreo
US10960381B2 (en) 2017-06-15 2021-03-30 Medtronic, Inc. Zirconium phosphate disinfection recharging and conditioning
US11278654B2 (en) 2017-12-07 2022-03-22 Medtronic, Inc. Pneumatic manifold for a dialysis system
US11033667B2 (en) 2018-02-02 2021-06-15 Medtronic, Inc. Sorbent manifold for a dialysis system
US11110215B2 (en) 2018-02-23 2021-09-07 Medtronic, Inc. Degasser and vent manifolds for dialysis
EP3542707A1 (fr) * 2018-03-20 2019-09-25 Gambro Lundia AB Appareil, capteur et procédé permettant de déterminer au moins un paramètre du sang circulant dans un circuit sanguin extracorporel
US11213616B2 (en) 2018-08-24 2022-01-04 Medtronic, Inc. Recharge solution for zirconium phosphate
US11806457B2 (en) 2018-11-16 2023-11-07 Mozarc Medical Us Llc Peritoneal dialysis adequacy meaurements
US11806456B2 (en) 2018-12-10 2023-11-07 Mozarc Medical Us Llc Precision peritoneal dialysis therapy based on dialysis adequacy measurements
EP3673929B1 (fr) * 2018-12-27 2023-09-27 Gambro Lundia AB Appareil pour traitement sanguin extracorporel
US11160503B2 (en) * 2019-04-23 2021-11-02 Fresenius Medical Care Holdings, Inc. Wearable continuous vascular access monitor
JP6783897B1 (ja) * 2019-05-09 2020-11-11 日機装株式会社 血液浄化装置
EP4046668A1 (fr) 2021-02-18 2022-08-24 Gambro Lundia AB Appareil de traitement extracorporel du sang
EP4098291A1 (fr) 2021-05-31 2022-12-07 Gambro Lundia AB Appareil de traitement extracorporel du sang
US11850344B2 (en) 2021-08-11 2023-12-26 Mozarc Medical Us Llc Gas bubble sensor
US11965763B2 (en) 2021-11-12 2024-04-23 Mozarc Medical Us Llc Determining fluid flow across rotary pump
US11944733B2 (en) 2021-11-18 2024-04-02 Mozarc Medical Us Llc Sodium and bicarbonate control
CN115328239A (zh) * 2022-07-29 2022-11-11 江苏汉邦科技股份有限公司 实验室用超滤设备及其实验方法
CN118370890A (zh) * 2024-06-27 2024-07-23 苏州阿基米德网络科技有限公司 一种血液透析系统

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997002057A1 (fr) 1995-07-04 1997-01-23 Hospal Ag Procede et appareil de dialyse automatique
EP1396274A1 (fr) 2002-09-05 2004-03-10 Gambro Lundia AB Contrôleur et méthode de contrôle pour un appareil de traitement sanguin
US20050045540A1 (en) 1991-04-19 2005-03-03 Connell Mark E. Method and apparatus for kidney dialysis
WO2006011009A2 (fr) 2004-07-23 2006-02-02 Gambro Lundia Ab Machine et procedure de traitement extracorporel du sang
US20070108129A1 (en) * 2005-11-11 2007-05-17 Nikkiso Co., Ltd. Hemodialysis apparatus and method for hemodialysis
US20080217245A1 (en) 2001-11-16 2008-09-11 National Quality Care, Inc. Enhanced clearance in an artificial kidney incorporating a pulsatile pump
WO2010004400A2 (fr) 2008-07-09 2010-01-14 Gambro Lundia Ab Appareil de traitement extracorporel du sang
US20110098625A1 (en) * 2008-05-26 2011-04-28 Gambro Lundia Ab Hemodialysis or hemo(dia)filtration apparatus and a method for controlling a hemodialysis or hemo(dia)filtration apparatus
US20140323942A1 (en) * 2013-02-28 2014-10-30 B. Braun Avitum Ag Fuzzy logic

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2145884C1 (ru) * 1992-11-12 2000-02-27 Алтин Медикал, Инк. Способ ввода рабочих команд в аппарат "искусственная почка" (варианты), устройство для выполнения гемодиализа

Patent Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050045540A1 (en) 1991-04-19 2005-03-03 Connell Mark E. Method and apparatus for kidney dialysis
WO1997002057A1 (fr) 1995-07-04 1997-01-23 Hospal Ag Procede et appareil de dialyse automatique
EP0778783A1 (fr) 1995-07-04 1997-06-18 Hospal Ag Procede et appareil de dialyse automatique
US5938938A (en) 1995-07-04 1999-08-17 Hospal Ag Automatic dialysis method and apparatus
US20080217245A1 (en) 2001-11-16 2008-09-11 National Quality Care, Inc. Enhanced clearance in an artificial kidney incorporating a pulsatile pump
EP1396274A1 (fr) 2002-09-05 2004-03-10 Gambro Lundia AB Contrôleur et méthode de contrôle pour un appareil de traitement sanguin
WO2006011009A2 (fr) 2004-07-23 2006-02-02 Gambro Lundia Ab Machine et procedure de traitement extracorporel du sang
US20070108129A1 (en) * 2005-11-11 2007-05-17 Nikkiso Co., Ltd. Hemodialysis apparatus and method for hemodialysis
US20110098625A1 (en) * 2008-05-26 2011-04-28 Gambro Lundia Ab Hemodialysis or hemo(dia)filtration apparatus and a method for controlling a hemodialysis or hemo(dia)filtration apparatus
WO2010004400A2 (fr) 2008-07-09 2010-01-14 Gambro Lundia Ab Appareil de traitement extracorporel du sang
US20140323942A1 (en) * 2013-02-28 2014-10-30 B. Braun Avitum Ag Fuzzy logic

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10342911B2 (en) * 2010-09-30 2019-07-09 Gambro Lundia Ab Apparatus for extracorporeal blood treatment
US10881779B2 (en) 2010-09-30 2021-01-05 Gambro Lundia Ab Apparatus for extracorporeal blood treatment
US11383012B2 (en) 2016-11-25 2022-07-12 Gambro Lundia Ab Apparatus for extracorporeal blood treatment
US10842924B2 (en) 2017-06-29 2020-11-24 Fresenius Medical Care Deutschland Gmbh Therapy control by comprehensive feedback
US12048790B2 (en) 2017-06-29 2024-07-30 Fresenius Medical Care Deutschland Gmbh Therapy control by comprehensive feedback
US10881347B2 (en) 2017-12-29 2021-01-05 Fresenius Medical Care Holdings, Inc. Closed loop dialysis treatment using adaptive ultrafiltration rates

Also Published As

Publication number Publication date
ITMI20110441A1 (it) 2012-09-22
EP2688601B1 (fr) 2015-07-15
WO2012172398A1 (fr) 2012-12-20
CN103547300B (zh) 2016-03-02
AU2012270067B2 (en) 2015-06-25
CA2830171A1 (fr) 2012-12-20
ES2547636T3 (es) 2015-10-07
CN103547300A (zh) 2014-01-29
US20140088483A1 (en) 2014-03-27
EP2688601A1 (fr) 2014-01-29
KR20130135961A (ko) 2013-12-11
KR101529414B1 (ko) 2015-06-16
AU2012270067A1 (en) 2013-10-31

Similar Documents

Publication Publication Date Title
US9199027B2 (en) Apparatus for extracorporeal blood treatment
US9220830B2 (en) Apparatus for extracorporeal blood treatment
US20200345922A1 (en) Apparatus for extracorporeal treatment of blood
EP2745863B9 (fr) Appareil pour traitement sanguin extracorporel
EP1926510B1 (fr) Automatisation et optimisation d'un traitement crrt par anticoagulation régionale au citrate
KR102013468B1 (ko) 유체를 체외 처리하기 위한 의료용 장치 및 유체의 수집 또는 전달을 위해 의료용 장치에서의 셋팅 유량을 계산하기 위한 방법
US10881779B2 (en) Apparatus for extracorporeal blood treatment
EP4098291A1 (fr) Appareil de traitement extracorporel du sang

Legal Events

Date Code Title Description
AS Assignment

Owner name: GAMBRO DASCO S.P.A., ITALY

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FONTANAZZI, FRANCESCO;SURACE, ALESSANDRO;PAOLINI, FRANCESCO;SIGNING DATES FROM 20131001 TO 20131008;REEL/FRAME:031704/0819

STCF Information on status: patent grant

Free format text: PATENTED CASE

MAFP Maintenance fee payment

Free format text: PAYMENT OF MAINTENANCE FEE, 4TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1551); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY

Year of fee payment: 4

MAFP Maintenance fee payment

Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY

Year of fee payment: 8